Removable stent-graft

ABSTRACT

A removable device such as a stent-graft, intended for applications where it may be desirable to remove the device at some time following implantation. The stent-graft of the present invention includes a helically-wound stent component provided with a covering of graft material. It is removable by gripping an end of the helically-wound stent component with a retrieval device and applying tension to the stent component in the direction in which it is intended to be withdrawn from the site of implantation. The use of such a retrieval device allows the stent-graft to be removed remotely, such as via a catheter inserted into the body at a different location from the implantation site. The design of the stent-graft is such that the stent component is extended axially while the adjacent portion of the graft separates between windings of the stent component. The axial extension of the stent component, with portions of the graft still joined to the stent component, allows the device to be “unraveled” (or “unwound”) and removed through a catheter of diameter adequately small to be inserted into the body cavity that contained the stent-graft. It is removed atraumatically, without incurring significant trauma to the body conduit in which it had been deployed.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.10/737,324 filed Dec. 16, 2003.

FIELD OF THE INVENTION

The present invention relates to the field of removable stent-grafts.

BACKGROUND OF THE INVENTION

Endoluminal stenting has provided a major advancement in clinicaltreatment modalities offering a significant reduction in perioperativetreatment times, iatrogenic injury, postoperative morbidity and healingtimes. Even with the unprecedented clinical advantages of these devices,there still remains a number of limitations and disadvantages of thetechnologies currently available. The two primary technologies availablefor endoluminal stenting are the use of bare metal stents and stentdevices provided with a covering or lining of a tubular graft material,i.e., stent-grafts. Either of these technologies may be made to bedeployed via inflation of a catheter balloon (e.g., stainless steelstents) or to be self-expanding (e.g., nitinol stents). All of thesetechnologies exhibit a common disadvantage in that none of thecommercially available devices are designed to be removable afterimplantation.

There are numerous applications for which a removable stent-graft wouldbe highly desirable. Even though great strides have been undertaken toenhance biocompatibility of these devices, it is still a synthetic,non-living tissue device that constitutes a foreign body. As a result,living tissue has a number of limitations and/or reactions in copingwith such a foreign body.

The most common of these is infection. Typically, when a syntheticdevice becomes infected, or colonized by bacteria, there is littlesuccess in resolving such an infected device or infected area short ofdevice removal from the patient. In some instances, if an infectedsynthetic device cannot be removed enabling the antibiotic treatment ofthe affected living tissue, patient mortality can result due to septicshock.

Another issue associated with implantation of endoluminal stents andstent-grafts is foreign body reaction. Endoluminal stents andstent-grafts are often employed to limit, or control, the body's normalhealing response (restenosis) to vascular, luminal, or ductal injury dueto balloon dilatation. Even though these devices aid in limiting theamount of restenosis as a result of vessel or ductal injury, after aperiod of time the vessel or duct may generate a hyperplastic tissue(restenotic) or calcific stone formation response due to the presence ofthe foreign body. Consequently, removal of the device after theappropriate therapeutic period may be desirable.

Still another application for a removable stent-graft would involveproviding a removable support structure for delivery of certain otherimplantable materials or structures (e.g., tubular structures) whichotherwise do not exhibit the necessary mechanical characteristics fordevice delivery without the aid of a temporary, supporting stentcomponent.

Further, mechanisms for localized drug delivery continue to be a highlysought after treatment option which offer many advantages over systemicdrug delivery. Two of the key challenges in local drug delivery are thedelivery mechanism and the drug elution profile or therapeutic window ofthe drug delivery. These are not unusually interrelated. By employingone or more applications of a removable drug eluting stent-graft,therapeutic windows can be greatly increased providing unlimited drugapplication profiles.

Thus, the array of clinical treatments modalities for such a removableendoluminal stent-graft includes: malignant and benign strictures of thebiliary tract due to tumor compression, anastomotic and bile stonenidus; anastomotic and benign strictures of the colon, small intestineand ureter/urethra; esophagus collapse syndrome and gastric refluxerosion; strictures of the tracheal/bronchial tree; treatment ofvascular disease or injury; and localized drug delivery for variouschemotherapy application.

Various designs for removable stents are known in the art. For example,Myler et al. in U.S. Pat. No. 5,474,563 describe a retrievable stent andretrieval tool. The described stent is removed intact, at its fullydeployed dimensions, and may consequently pose a risk of trauma duringremoval.

U.S. Pat. No. 5,782,903 to Wiktor et al. describes a removable stentsystem which comprises a continuous serpentine wire formed into helicalcoil. The coil after implantation can be uncoiled by use of a retrievalline. Beyar et al. in U.S. Pat. No. 6,090,115 also describe a temporarystent system comprising a stent constructed of a helical coil ofbiocompatible material. Both of these references teach that the stent isnot covered (i.e., is not a stent-graft) and therefore providesopportunity for tissue in-growth into the spaces between the coilstructure over time. This in-growth may result in trauma to the implantsite during retrieval.

U.S. Pat. No. 5,799,384 to Schwartz et al. teaches a stent similar tothe above-described Wiktor et al. stent. It differs from the Wiktor etal. stent in that a tape of polymeric film is provided to the stentwire, the length of the tape running parallel to the length of the wirewith the width of the tape being centered over the stent wire andtherefore extending perpendicularly from the stent wire a short distancefrom both sides of the wire. When the wire is wound into a helical formto create a stent structure, the polymeric tape provides a sort of graftcovering. However, this graft covering is discontinuous and thereforecannot offer the advantages of a continuous graft covering extending forall or a major portion of the length of the implantable stent structure.

Huxel et al. in U.S. Pat. No. 6,494,908 describe a removable stent inthe form of a helical winding wherein adjacent windings are in directcontact; removal is accomplished by grasping an end of the helix andunwinding the helical form. The helical form of the Huxel et al. deviceis made from a soft, flexible fiber that is provided with an outercoating of a bioabsorbable material to render it rigid for insertioninto a body conduit. The device becomes thinner and flexible over timein order to allow the stent to be removable after a pre-determined timehas passed. U.S. Pat. No. 5,514,176 to Bosley et al. teaches a somewhatsimilar device in the form of a removable stent-graft made from a seriesof helical windings with the adjacent windings in contact with eachother. An exterior coating of silicone is provided to seal between theadjacent windings. Removal is accomplished by unwinding the devicewhereby the coating is removed simultaneously with the helical winding.

Camrud et al., in U.S. Pat. No. 6,258,117, teach a multi-section stentwhich incorporates a connecting structure that can separate. Thisability to separate adjacent segments of the connecting structurehowever is promoted as a means to add flexibility to the implanteddevice rather than as a way to atraumatically remove portions of it.Removability of the segments is not taught or suggested. Iwasaka et al.in US Patent Application Publication No. 2003/0114922 describe astent-graft having a series of discrete, ring-like stent structuresalong its length. The device is removed from a body conduit by graspingits distal end with a retrieval device and everting it from the distalend by pulling it through itself in a proximal direction. The device isremoved in its entirety rather than being removed segmentally.

WO00/42949 teaches the construction of an impermeable stent-graft thatis primarily intended for biliary applications. This stent-graft is notdescribed as being removable.

SUMMARY OF THE INVENTION

The present invention relates to removable, implantable devices such asremovable stent-grafts or removable filter devices (e.g., embolicfilters or vena cava filters). Such devices are intended forapplications wherein it may be deemed necessary to remove the device atsome time following implantation. Such applications may includestent-grafts for implantation in urethras, in biliary ducts, in thevascular system, the large or small intestine, or in the esophagus ortrachea. It may be desirable for a stent-graft to be removable inapplications where the stent-graft has been inserted to preventobstruction of a duct by anastomotic stricture or by a tumor,particularly prior to determining if the tumor is malignant or benign.It may be desirable for such a stent-graft to be removable if itsintended purpose was temporary, such as for delivery of a therapeuticagent such as drugs or radioactive materials to a specific site for alimited time. It may be also be of value to enable the stent-graft to beremoved in the event that it does not effect its intended purpose andmust be replaced by another device.

Devices of the present invention comprise a structural support, such asa stent component, provided with a covering of a graft material.Adjacent elements of the structural support are spaced apart, i.e., notin continuous direct contact with each other when the device is in arelaxed state without any deforming force applied to it. The coveringgraft material generally extends between the ends of the device andcovers the spaces between the adjacent elements of the structuralsupport.

The stent-graft of the present invention has a continuous luminalsurface, meaning that, prior to removal, the graft material covering thestent component extends in a substantially continuous fashion betweenthe opposing ends of the device. While the graft material may beseparable between adjacent windings of the stent component duringremoval (as by splitting or tearing) as will be further described, thegraft material is substantially integral prior to removal and does notinclude gaps between adjacent windings of the stent component (as shownby, for example, U.S. Pat. No. 5,799,384) prior to removal. Thecontinuous luminal surface does not preclude the possibility of openingsthrough portions of the graft material at desired locations for purposesof the particular stent application.

The graft material covering the stent component may be provided on theexterior surface of the stent component, the luminal surface of thestent component, or may cover both the exterior and luminal surfaces.

The device of the present invention is removable by gripping an end ofthe helically-wound structural support with a retrieval device andapplying tension to the structural support in the direction in which itis intended to be withdrawn from the site of implantation. The design ofthe device is such that the structural support (e.g., stent component)is extended axially while the adjacent portion of the graft separatesbetween windings of the structural support. For a stent-graft, forexample, the axial extension of the stent component, with adjacentportions of the graft still joined to the stent component, allows thedevice to be “unraveled” (or “unwound”) and removed through a catheterof diameter adequately small to be inserted into the body cavity thatcontained the previously-deployed stent-graft.

The stent-graft is cohesively removable (i.e., is cohesivelydisassembled), meaning that it is removed in its entirety, without lossof pieces or the formation of separate remnants during the removal(e.g., the unraveling) process.

The stent-graft is remotely removable, in that it may be grasped at oneend for removal by a retrieval device inserted from a more distant pointof entry into a body. Further, the removal is substantially or entirelyatraumatic to the body conduit in which the device had been originallydeployed. This is because the unravelable stent graft lends itself toremoval with minimal force and to being removed through a relativelysmall diameter catheter.

This “unravelable” stent component may also enable the delivery of anintraluminal graft to an intended site and deployment of theintraluminal graft securely against the luminal surface of that site.Following deployment, the stent component may be removed (simultaneouslywith the delivery system, or alternatively, separately removed at alater time), leaving the graft component implanted at the site.

In still another embodiment, the stent-graft of the present inventionmay be delivered and deployed at a desired site, with permanentlyattached but separate stent components also deployed and intended to beleft implanted permanently at, for example, the ends of the stent-graft.Another stent component extending along the remaining length of thedevice not supported by the permanent stent components may then beremoved following successful deployment and implantation. This temporarystent component may be useful, for example, to assure that the device isimplanted without twisting or other misalignment, and thus removed onceit has served its temporary purpose.

Still further, the stent-graft or the stent component thereof may bemade to be removable in lengthwise sections or segments.

The stent component is preferably metallic and more preferably isstainless steel or nitinol. It may be balloon expandable orself-expanding. The graft material that covers the stent component maybe of a variety of implantable materials such as nylon, polyethyleneterephthalate or polytetrafluoroethylene, and is preferably of expandedpolytetrafluoroethylene (ePTFE) made as taught by U.S. Pat. No.3,953,566 to Gore. Alternatively, either or both of the stent componentand the graft component may be made of any of a variety of resorbablematerials. These resorbable materials may optionally be used incombination with various non-resorbable materials for particularapplications as desired.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1 and 1A are perspective views of stent-grafts of the presentinvention showing the stent component provided with a thin, flexiblecovering of graft material.

FIG. 2 shows a perspective view of the stent-graft during removal froman implant site by being cohesively disassembled via pulling the endfitting through a retrieval catheter by use of a remotely operatedinstrument.

FIGS. 3 and 3A-3D show side views of alternate embodiments of engagementfittings that protrude from either or both ends of the stent-graft.

FIGS. 4A-4D show side views of various means of weakening the graftcovering material to allow it to separate between adjacent windings ofthe stent component during removal of the stent-graft.

FIGS. 5A-5C illustrate side views of a stent-graft having multipleengagement fittings that coincide with controllably disruptable patternsin the graft material, allowing the graft to be removed in lengthwisesegments.

FIGS. 6A-6B show longitudinal cross sections of an alternativeembodiment wherein the stent-graft has a luminal liner that is removableat a time subsequent to implantation, while the remainder of thestent-graft is left in place.

FIG. 7 shows a longitudinal cross section of an alternative embodimentwherein the stent component is secured to the graft material by aresorbable adhesive that allows for removal of the stent component at atime subsequent to insertion and deployment of the stent-graft.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 is a perspective view of the device 10 of the present inventionwherein the device is composed of a structural component such as stentcomponent 14, provided with a thin, flexible covering of graft material18. The graft material 18 can be either impermeable or permeabledepending upon the needs of the application. An impermeable materialwould prevent the transmission of fluids and/or cells, such as bileand/or tumor or epithelial cells, through the graft material while apermeable material would allow the transmission of fluids through thegraft material. It is also possible to laminate one or more layers of aporous or permeable material to one or more layers of impermeablematerial. This may be done, for example, where the porous material isdesired to provide for tissue attachment to one or both surfaces, whilesimultaneously providing a construction that is fluid impermeablethrough its thickness. Generally, impermeable coverings are preferredfor biliary applications or applications wherein it is desired toinhibit or preclude cellular ingrowth.

In the embodiment shown by FIG. 1, the stent component 14 comprises wirewhich has been formed into a serpentine shape having apices 22, whichshape is also helically wound into a tubular form. The radii of theapices 22 of the serpentine shape can be as large or small as desiredfor an intended application. Minimal radii result in the serpentineshape having relatively pointed apices 22, i.e., a zig-zag form.Attached to the wire at the ends are engagement fittings 26, whichextend from either or both ends of the device 10. These engagementfittings 26 may be grasped by or attached to a surgical instrument toprovide for removing (e.g., by cohesively disassembling) the device 10during remote atraumatic removal of device 10 from a patient in situthrough a small diameter working catheter or sheath. Removal of device10 will be described in further detail.

The wire used to fabricate stent component 14 is preferably nitinol wireof, for example, about 0.23 mm diameter. A preferred nitinol wire iswire of this diameter (available from Nitinol Devices & Components Inc.,Fremont Calif.) that has been 45% cold worked and electropolished. Mostpreferably, the stent component is formed from a single length of wirefor simplicity and lowest possible profile. One method of forming thewire into the desired serpentine shape is to use a mandrel of similardiameter as the intended diameter of the desired tubular form of thestent-graft. The mandrel is provided with appropriately located pinswhich protrude radially from the exterior surface of the mandrel inlocations corresponding to the intended locations of the apices of theserpentine shape. A suitable length of the wire is then wrapped aroundthe pins protruding from the mandrel surface creating the helicallywound serpentine shape that results in the form of stent component 10.Selected pins pertaining to optional raised apices 22 r may be placed onappropriately elevated surfaces to achieve the desired amount ofelevation. The general form of and method of making such a wire stentare described in WO 97/21403 (see, e.g., FIGS. 1A-2 of WO 97/21403 forthe wire form which for purposes of the present invention does notrequire the additional coupling member 8 or linking member 20). Thiswire and mandrel assembly may be placed into an oven for any desiredheat-treating. Immediately following removal from the oven, the wire andmandrel assembly is quenched in water at about room temperature,following which the formed stent is removed from the mandrel.

FIG. 1 also shows how the adjacent windings (or adjacent elements) ofthe helically-wound stent component are spaced apart, with the graftmaterial covering the space between the adjacent windings. It is notrequired that the space between adjacent windings is covered in itsentirety by the graft material, although full coverage of these spacesbetween the adjacent elements of the stent component is generallypreferred. The space between adjacent windings or elements of the stentcomponent exists when the stent is in a relaxed state, not subjected tolongitudinal compression that could force the adjacent elements to be incontact and therefore no longer spaced apart.

The use of the serpentine winding of stent component 14 shown in FIG. 1allows the completed stent to be deployed with minimal foreshortening.The stent-graft 10 of the present invention, when deployed from itssmall, insertion diameter to its largest, fully deployed diameter, willforeshorten less than about 10% of its insertion length. It is alsocapable of foreshortening less than about 8%, 6%, 4%, 2% or even 0%depending on construction details when properly deployed. Alternatively,if desired, the stent-graft may be made to be controllablyforeshortenable during deployment, in significant length amounts, in theinterest of making a length-adjustable device. The use of a flexiblegraft material in conjunction with the arrangement of adjacent apices inthe windings of the stent component can allow the device to becontrollably shortened in length during deployment, if desired. It can,for example, be controllably foreshortenable by the physician duringdeployment in an amount equal to about 20% or more of the fully extendedlength of the device (after being extended by light manually appliedaxial tension, followed by removal of the tension). It is also possibleto provide the device in a form that can be controllably foreshortenableby the physician during deployment in an amount equal to about 50% ormore of the fully extended length of the device.

As also shown by FIG. 1, some of the apices 22 r of the serpentine-woundwire may be raised above the tubular form so that they protrude somewhatabove the outer surface of the remainder of the stent-graft. Theseprotruding or raised apices 22 r may be useful as anchoring means forthe covered stent 10 in that they will protrude slightly into the wallof any body conduit into which the stent-graft is implanted. In apreferred embodiment for biliary applications, the raised apices 22 rare generally located at locations other than at the extreme ends of thestent; they are typically no closer than about 1 mm to the ends of thestent. These raised apices 22 r are preferably formed during the formingof the stent wire (preferably nitinol wire and more preferably a singlenitinol wire) into the desired serpentine, helically wound shape usedfor the stent component 14. Further, as shown by the perspective view ofFIG. 1A, these raised apices 22 r, may optionally be covered with graftmaterial 18 so as to prevent in-growth of tissue into the wire meshstructure (i.e., overgrowth or encapsulation of the apice 22 r by livingtissue). Prevention of tissue in-growth into the mesh structure wouldfacilitate atraumatic removal of the device 10, even if the device hadnot been made to be removable by unraveling as described below.

It is apparent that there are a variety of ways of orienting the raisedapices to achieve differing desired amounts of anchoring of the deployedstent-graft. Variables include the angle of deviation of apices fromparallel to the longitudinal axis of the stent component, the number ofraised apices, the height of raised apices, and whether all or anyportions of particular apices are raised.

It is generally preferred that raised apices alternate with adjacentapices which are not raised (i.e., adjacent on the same continuoussection of stent wire) in the interest of providing a good bond betweenthe stent component and covering graft material. This is particularlytrue with respect to the embodiment of FIG. 1 and is less critical withregard to the embodiment of FIG. 1A.

Finally, it is apparent that the use of raised apices as described isonly one means of providing anchoring for a stent-graft. It is furtherapparent that, for some applications, anchoring means such as apices maybe undesirable.

The attachment of the covering material to the stent component may beaccomplished by methods including those described by U.S. Pat. No.5,735,892 to Myers et al. Mechanical attachment may be by methods suchas by the use of sutures. The covering material will preferably beattached to the stent using an adhesive such as, for example,fluorinated ethylene propylene (FEP) which is effective as a meltablethermoplastic adhesive. It is apparent that a variety of adhesives maybe used (including thermoset adhesives) as long as the adhesive chosenis adequately biocompatible. The adhesive may be applied to the stent ineither solid (powdered) or liquid form by various methods includingpowder coating, dipping or spraying. Liquid forms may be diluted ifdesired with appropriate solvents as necessary for the chosen method ofapplication. The adhesive-coated stent component may be heated to ensureuniform coating of the stent component by causing melting of thethermoplastic adhesive.

Alternatively, the coating material applied to the ePTFE film from whichthe stent covering is made, may also be relied on for joining of thegraft material to the stent component.

FIG. 2 illustrates the device 10 being cohesively disassembled duringremoval from the body conduit into which it was previously implanted, bymeans of the end fitting 26 being pulled through a retrieval catheter 30by use of a remotely operated instrument such as removal tool 27.

As shown, the thin, flexible covering material (graft material 18) isdisrupted by the tensile force applied to the stent-graft 10 by theremotely operated instrument 27. As the graft material 18 is disrupted,it remains cohesively attached to the adjacent portion (or element) ofstent component 14 which is simultaneously being uncoiled. Thisdisruption, or unraveling, of the graft material 18 and uncoiling ofstent component 14, results in minimal trauma to the vessel from whichit is being removed as the stent coil diameter is reduced from itsexpanded state during the disassembling and retrieval process. Further,the graft material 18, attached to the stent component 14, forms into athin ribbon which fits into a capturing catheter that has beenpositioned in close proximity to the end of the implanted device 10.This thin ribbon resulting from the unraveling process may have a lengththat is 100%, 200%, 300%, 400%, 500% or even greater than the length ofthe deployed stent-graft prior to removal.

The retrieval catheter 30 need only be adequately large diametrically toaccommodate the anticipated width of the strip of the stent-graft beingremoved, i.e., adequately large to accept the substantially straightenedserpentine wire form with a small amount of attached graft material. Thecatheter thus may be smaller in outside diameter than the catheter usedpreviously to initially deliver and implant the device, and likewisesmaller than the compacted diameter of the stent-graft itself duringdelivery to the implantation site (prior to diametrical expansion of thestent-graft during deployment, i.e., the small delivery profile).

FIGS. 3 and 3A-3D show alternate embodiments of the engagement fittings26 that protrude from either or both ends of the device 10. Thesefittings facilitate secure attachment of the ends of the device 10 to anappropriate tool (e.g., removal tool 27) for use in initiating andcompleting the cohesive disassembly of the device 10. Examples ofengagement fittings 26 include a ball as shown in FIG. 3A, a loop asshown in FIG. 3B, a swaged-on end piece as shown in FIG. 3C and athreaded end as shown in FIG. 3D. Other shapes, providing the samefunction of allowing a removal tool to grasp, attach, or otherwisesecurely engage onto the fittings 26, could be used as well. It isapparent that the designs of the engagement fitting 26 and removal tool27 (not shown in FIGS. 3-3D) must be compatible in order to enable thetool 27 to effectively grasp and apply tension to the engagement fitting26.

Numerous means for rendering the graft material 18 able to be cohesivelydisassembled can be contemplated. FIG. 4A shows a device 10 wherein thegraft material 18 is selectively weakened in a prescribed pattern 34.The graft material 18 may be weakened in those areas 34 by mechanicalmeans such as a cutting with a blade or compressing die. Alternativelythe graft material 18 may be weakened by use of energy such as with alaser or controlled heating. While the patterns 34 may extend entirelythrough the wall of the graft material 18, it is preferred that theyonly extend through a portion of the thickness of the graft material.

FIG. 4B shows a device 10 wherein the graft material 18 is selectivelyweakened by perforating the graft material in an alternative prescribedpattern 38. The graft material 18 may be perforated using numerousmeans, such as with a mechanical cutting blade, a cutting die, a laser,or heat. Perforations 38 may extend entirely through the thickness ofthe graft material 18, or only extend through a portion of thatthickness. When a multi-layer graft material 18 is used, theperforations can be made through one layer, but not through all layers,thereby preventing tissue in-growth through the graft material 18.

FIG. 4C shows a device 10 wherein a graft material 18 is provided havinga node 42 and fibril 44 microstructure (e.g., ePTFE), of which a smallsample area 18 e, is shown enlarged. This graft material 18 is orientedso as to be weaker in the longitudinal direction than in the radial(circumferential) direction. The ePTFE microstructure shown has auniaxial microstructure, meaning that the fibrils are oriented primarilyin a single direction. The graft material is thus amenable to splittingin the same direction as its direction of greatest strength (i.e., thedirection of orientation of the fibrils). This orientation allows forthe possibility of the graft material 18 splitting or separating betweenadjacent windings of the stent component 14 during removal of the stentin the manner previously described (i.e., cohesively disassembling). Apreferred method of using such a node and fibril microstructure graftmaterial is to use a film such as an ePTFE film, that has been cut intoa long, narrow tape with the length of the tape parallel to thedirection of the fibrils. This tape can be used as a graft coveringeither over or beneath the stent component 14, or both over and beneathstent component 14, and is applied as a helical wrap with the pitch ofthe helix equal to and parallel to that of the helical pitch of theserpentine stent wire. This allows for disruption of the graft material18 parallel to the pitch of the serpentine stent winding 14, bysplitting of the tape parallel to its length (i.e., parallel to thedirection of the fibrils) during stent removal, generally as shown byFIG. 2.

The use of a covering graft material with anisotropic strengthproperties wherein the graft material is oriented with the direction ofgreatest strength in the circumferential direction (as described abovewith the ePTFE film) provides the resulting stent-graft with good hoopstrength. Following deployment at a desired site, such a device may beamenable to further expansion using a balloon catheter if it is deemednecessary by the physician.

FIG. 4D shows a device 10 wherein the graft material 18 is constructedfrom a composite of resorbable and non-resorbable materials. Theresorbable materials, which may be desirably located in selected areasof the device 10 such as in a line between and parallel to adjacentelements of stent component 14 (similar to the line of perforations 38of FIG. 4B), are degraded and absorbed by the body. One such resorbablegraft material is taught by U.S. Pat. No. 6,165,217 to Hayes; thismaterial takes the form of a fibrous web as shown by the enlargement of18 e ₂. Resorbtion times are typically a function of the resorbablepolymer chosen and the thickness of the material. After the resorbablematerials have been degraded, weakened areas are formed in the remainingnon-absorbable sections of the graft material 18. These weakened areasare more easily disrupted when longitudinal force is applied to anengagement fitting 26, allowing the device 10 to be cohesivelydisassembled. In addition to the methods described herein, it isapparent that various other methods of selectively weakening the graftmaterial may be contemplated.

Another embodiment of this invention provides for partial disassembly ofthe device 10 in situ to allow for shortening of the overall devicelength, wherein one or more pieces of the device may be cohesivelydisassembled from the remainder of the stent-graft. FIGS. 5A-5Cillustrate a device 10 which has multiple engagement fittings 26, thatcoincide with controllably disruptable patterns in the graft material18. The amount of force needed to cause disruption of the graft material18 and therefore separation of segments of the device 10 can be variedbetween segments of the device. These disruptable patterns could bearranged so as to have the most easily disrupted pattern 52, closest tothe remotely operated removal instrument, with the next most easilydisrupted pattern 56, further away from the remotely operated removalinstrument. Consistent with this arrangement, the pattern requiring themost force for disruption 58, would be located furthest away from theremotely operated removal instrument. Sequential removal of the segmentsof the device 10 is described in the sequence shown from FIG. 5A to FIG.5C, wherein FIG. 5A shows the device as implanted with all threesegments. FIG. 5B shows the device 10 after removal of the firstsegment; FIG. 5C shows the device after removal of the first and secondsegments. The segments are removed cohesively, meaning that theyseparate discretely without loss of fragments or pieces. It is apparentthat such a device may be provided with a number of segments as desired.

FIGS. 6A-6B show longitudinal cross sections of an alternativeembodiment wherein the stent-graft 10 has a luminal liner 18 a that isremovable at a time subsequent to implantation, while the remainder ofthe stent-graft 10 is left in place. Liner 18 a is provided with apull-tab or engagement fitting 26 at the distal end of liner 18 a. Asshown by FIG. 6B, engagement fitting 26 may be grasped by a removal tool27. The application of tension to engagement fitting 26 via tool 27allows the liner 18 a to be everted and removed through the lumen ofstent-graft 10 and the body conduit in which the stent-graft 10 has beenpreviously deployed. This embodiment may be desirable for applicationsin which, for example, the luminal graft layer 18 a has been providedwith a drug coating intended for delivery to the site of implantation.It may be desired to subsequently remove layer 18 a following a timesuitable for the elution of the drug coating. It may also be desirableto have this luminal layer 18 a removable to expose the luminal surfaceof layer 18, which may optionally also be provided with a drug coatingof the same drug, or of an entirely different drug.

FIG. 7 shows a longitudinal cross section of an alternative embodimentwherein the stent component 14 is secured to the graft material 18 by aresorbable adhesive 72 that allows for removal of the stent component ata time subsequent to insertion and deployment of the stent-graft. Thematerial of the resorbable adhesive may be chosen for a desired timeafter which the stent component may be removed. This may be useful if,for example, the stent component is intended to deliver a drug to theimplantation site and then removed subsequent to elution of the drugcoating applied to the stent. Alternatively, it may be desirable toremove stent component 14 after graft material 18 has had adequate timeto attach (e.g., via tissue ingrowth) to the luminal surface of the bodyconduit into which it has been implanted.

Other short-term adhesives are also possible, such as hydrogels (e.g., a5% solution of polyvinyl alcohol, by weight volume in water). These maybe useful, for example, to join together parts of a stent-graft where itmay be desired to include components in the construction that arenecessary for implantation and deployment, but not needed functionallyfollowing deployment. Such components might be longitudinally orientedstruts that would ensure that the device is implanted without beingtwisted. Once deployed, these longitudinally oriented struts could beremoved so as not to occupy space within the lumen of the device. Thesecomponents could be joined to the stent-graft during manufacturing by atemporary adhesive such as a hydrogel, which would be designed todissolve upon exposure to warm body fluids within a relatively shorttime such as about 15 minutes, after which they could be removed fromwithin the device. Removal could be accomplished with removal devices aspreviously described.

Example

A stent component was produced by winding a 0.25 mm diameter nitinolwire (SMA Inc, Santa Clara Calif.) onto an 8 mm diameter wire formingfixture, creating a stent component as shown in FIG. 1. The wire-woundfixture was then subjected to heat treatment and quench cyclessufficient to set the wire into the desired form. FEP powder (DaikinAmerica, Orangeburg N.Y.) was applied to the stent component by firststirring the powder into an airborne “cloud” in a standard kitchen-typeblender and suspending the frame in the cloud until a uniform layer ofpowder was attached to the wire. The stent component was then subjecteda thermal treatment of 320° C. for approximately one minute to cause thepowder to melt and adhere as a coating over the stent component.

A sacrificial 7 mm inside diameter, 0.1 mm thick ePTFE tube that hadbeen previously heated above 380° C., was pulled onto an 8 mm diametermandrel, which involved slight stretching of the ePTFE tube. This tubewas intended to serve as a release aid when stripping the finalconstruct from the mandrel and would subsequently be discarded.

One layer of a thin ePTFE film provided with a discontinuous coating ofFEP was then wrapped around the sacrificial tube. The ePTFE film was ofa type produced in accordance with U.S. Pat. No. 5,476,589 to Bacino; ithas a greater strength in the longitudinal direction than in thetransverse direction. This film was further modified by application of adiscontinuous coating of FEP as taught in U.S. Pat. No. 6,159,565 toCampbell et al. The film was applied with the ePTFE side down (towardthe mandrel) and with the direction of greater strength orientedcircumferentially (i.e., perpendicular to the longitudinal axis of themandrel). Edges of the film (parallel to the longitudinal axis of thetube and mandrel) were slightly overlapped.

The stent component was carefully fitted over the ePTFE film and tubecovered mandrel. Localized heat from a soldering iron was then appliedto the wire, causing the FEP wire coating to re-flow and attach to theFEP-coated ePTFE film. When the entire stent component had been joinedto the underlying ePTFE film in this manner, one additional layer of thesame FEP-coated ePTFE/FEP film is applied over the stent frame. Thisouter film layer was applied with the FEP side down toward the stent andwith the direction of greater strength oriented circumferentially(perpendicular to the longitudinal axis of the mandrel). Longitudinaledges of the film were again slightly overlapped.

The mandrel and construct residing upon it was then subjected to athermal treatment in an air convection oven set at 320° C. for 5minutes. After removal from the oven and being allowed to cool to aboutambient temperature, the stent-graft was stripped from the mandrel andthe sacrificial ePTFE tube was removed from within the stent-graft anddiscarded. The graft ends were then trimmed as necessary using scissors.

The resulting 8 mm diameter stent-graft was chilled by spraying withMicro Freeze™ (Micro Care Corp., Bristol CT) and then diametricallycompacted at a temp of −10° C. in a refrigeration chamber. Compactionwas effected using a collet or iris type of diametrical compactiondevice, such as taught by U.S. Pat. No. 6,629,350. The stent-graft wascompacted only to a diameter of about 4 mm, adequate to allow it to beinserted into a length of silicone tubing was intended to simulate thelumen of a biliary duct. This silicone tubing (part no. T050PLAT256×236,Jamak Corp., Weatherford Tex.) was of about 6 mm and about 0.25 mm wallthickness. After insertion of the entire length of the stent-graft intothe lumen of the silicone tubing, the stent-graft was deployed withinthe tubing, gripping the luminal surface of the tubing.

The resulting 8 mm diameter stent-graft was demonstrated to be easilyand completely removed through the application of a tensile forceapplied to the device. Removal was effected using a Cordis Brite Tip™ 5french guide catheter through the proximal end of which had beeninserted a length of 0.2 mm diameter nitinol wire that had been doubledback on itself. When the doubled wire was fully inserted, the doubledend of the wire was allowed to extend a short distance beyond the distaltip of the catheter while the two free ends extended from the proximalend. The wire-containing catheter shaft was then inserted into a lengthof translucent polymer tubing of 2.5 mm inside diameter and 0.035 mmwall thickness. The doubled end of the wire, forming a small loop, wasplaced over the engagement fitting located at the end of the stentcomponent, after which tension was applied to the wire and catheterassembly by pulling on the proximal end of that assembly with respect tothe translucent polymer tube through which it had been inserted. Duringthe application of this tensile force to the stent, the silicone tubingcontaining the stent was held restrained (resisting the tensile force)in a human hand. The wire-and-catheter assembly was slowly withdrawn ina proximal direction, into the translucent polymer tube. The tensileforce, applied to the engagement fitting located at the end of the stentcomponent, caused the stent-graft to unravel and be cleanly withdrawninto the translucent polymer tube, generally as shown by FIG. 2. Thistensile force was applied until the entire stent-graft had beenwithdrawn. Withdrawal was accomplished with minimal distortion orelongation (i.e., minimal trauma) to the silicone tube. No separateremnants of the stent-graft resulted from the removal by unravelingprocess.

While particular embodiments of the present invention have beenillustrated and described herein, the present invention should not belimited to such illustrations and descriptions. It should be apparentthat changes and modifications may be incorporated and embodied as partof the present invention within the scope of the following claims.

1. An endoprosthesis comprising: a stent component having opposing endsand further having a small delivery profile and an enlarged deployedprofile; said stent component comprising a wire formed into a generallyhelical winding having space between adjacent elements of the generallyhelical winding, wherein the generally helical winding provides agenerally tubular form to the stent component and wherein the generallyhelical winding includes at least one apex located between the opposingends of the stent component; a graft material attached to the stentcomponent covering the space between adjacent elements of the generallyhelical winding, wherein the graft material provides a continuousluminal surface; and wherein at least one of said apices located betweenthe opposing ends of the stent component is raised to protrude outwardlyfrom said tubular form and wherein the resulting raised apex is coveredby said graft material.
 2. The endoprosthesis of claim 1 whereinfollowing deployment, the endoprosthesis is adapted to be cohesivelydisassembled to allow for its remote removal from a patient.
 3. Theendoprosthesis of claim 1 wherein at least a portion of the generallyhelical winding has a serpentine form with alternating opposing apices.4. The endoprosthesis of claim 3 wherein following deployment, theendoprosthesis is adapted to be cohesively disassembled to allow for itsremote removal from a patient.
 5. The endoprosthesis of claim 1 whereinsaid graft material is impermeable to body fluids.
 6. The endoprosthesisof claim 1 wherein said graft material is ePTFE.
 7. The endoprosthesisof claim 6 wherein said graft material is ePTFE provided with a coatingof FEP.
 8. An endoprosthesis comprising: a stent component havingopposing ends and further having a small delivery profile and anenlarged deployed profile; said stent component comprising structuralelements and space between adjacent structural elements, wherein thestructural elements provide a generally tubular form to the stentcomponent and wherein the structural elements include at least one apexlocated between the opposing ends of the stent component; a graftmaterial attached to the stent component covering the space betweenadjacent structural elements, wherein the graft material provides acontinuous luminal surface; and wherein at least one of said apiceslocated between the opposing ends of the stent component is raised toprotrude outwardly from said tubular form and wherein the resultingraised apex is covered by said graft material whereby encapsulation ofthe raised apex by living tissue is prevented.
 9. The endoprosthesis ofclaim 8 wherein following deployment, the endoprosthesis is adapted tobe cohesively disassembled to allow for its remote removal from apatient.
 10. The endoprosthesis of claim 8 wherein at least a portion ofthe generally helical winding has a serpentine form with alternatingopposing apices.
 11. The endoprosthesis of claim 10 wherein followingdeployment, the endoprosthesis is adapted to be cohesively disassembledto allow for its remote removal from a patient.
 12. The endoprosthesisof claim 8 wherein said graft material is impermeable to body fluids.13. The endoprosthesis of claim 8 wherein said graft material is ePTFE.14. The endoprosthesis of claim 13 wherein said graft material is ePTFEprovided with a coating of FEP.